JP6933031B2 - Ultrasonic probe and ultrasonic diagnostic equipment - Google Patents

Description

The present invention relates to an ultrasonic probe and an ultrasonic diagnostic apparatus.

Conventionally, an ultrasonic diagnostic apparatus has been known that generates an ultrasonic image of the internal structure of a subject by irradiating the inside of the subject with ultrasonic waves, receiving the reflected ultrasonic waves, and performing predetermined signal data processing. ing. Such an ultrasonic diagnostic apparatus is widely used for various purposes such as inspection for medical purposes, treatment, and inspection of the inside of a building structure.

The ultrasonic diagnostic device not only displays an ultrasonic image, but also collects a sample of a specific part (target) in the subject, discharges water, etc., or a drug, a marker, etc. at a specific part. It is also used when inserting the puncture needle toward the target position while visually recognizing the puncture needle used for these and the position of the target when injecting or indwelling. By using such an ultrasonic image, it is possible to quickly, reliably and easily perform treatment on a target in a subject.

In the ultrasonic diagnostic apparatus, oscillators that transmit and receive ultrasonic waves are arranged in a one-dimensional or two-dimensional matrix, and while scanning the position and direction of transmitting and receiving ultrasonic waves in a predetermined arrangement direction (particularly, electronic scanning). Most of them are used for imaging. The puncture needle is inserted along this scanning direction (lateral direction) by the operation of an operator such as a doctor, so that the puncture needle is continuously imaged from the insertion position to the subject to the arrival at the target. Located in the possible range. Previously, the puncture needle was attached to an attachment fixedly connected to an ultrasonic probe called a puncture guide and inserted, but now the operator can insert the puncture needle freehand. There are many.

Therefore, the puncture needle may not always accurately face the initial puncture direction or the puncture needle may be curved depending on the internal state, structure, tip shape of the puncture needle, and the like of the subject. As a result, the tip of the puncture needle may deviate from the range that can be imaged in the elevation direction perpendicular to the scanning direction, and imaging may not be performed. In addition, even when simply obtaining a cross-sectional image without using puncture, if the operator is unfamiliar, when changing the posture of the ultrasonic probe to fine-tune the imaging range in the elevation direction. However, there are cases where appropriate changes cannot be made and it takes time and effort to obtain a desired image.

Therefore, in an ultrasonic probe in which a plurality of vibrators are arranged in two dimensions, a delay circuit that inputs and receives a transmission / reception signal to each of the plurality of vibrators in the short axis direction perpendicular to the long axis direction of the arrangement. And a deflection control circuit with a deflection changeover switch is provided, and the timing of the transmission signal is shifted by the deflection control circuit, and the ultrasonic beam is deflected in the minor axis direction by adding a delay to the received signal to shorten the ultrasonic beam from the target. An ultrasonic diagnostic apparatus for displaying an axially deviated puncture needle is known (see Patent Document 1).

Further, in an ultrasonic probe in which a plurality of vibrators are arranged in two dimensions and the whole is covered with an acoustic lens having substantially the same curvature, the plurality of vibrators are divided in the minor axis direction, and some of the divided vibrations are vibrated. An ultrasonic diagnostic apparatus is known that uses a group of children for transmission and reception to deflect an ultrasonic beam in the minor axis direction and display an puncture needle deviated from the target in the minor axis direction (see Patent Document 2).

Japanese Unexamined Patent Publication No. 2000-139926 Japanese Unexamined Patent Publication No. 2016-47191

However, the ultrasonic diagnostic apparatus described in Patent Document 1 requires a delay circuit for each vibrator for ultrasonic beam deflection, and the size, cost, and calorific value of the apparatus are large.

Further, the ultrasonic diagnostic apparatus described in Patent Document 2 does not require the delay circuit, and the size, cost, and calorific value of the apparatus do not increase. However, since the ultrasonic diagnostic apparatus described in Patent Document 2 uses acoustic lenses having substantially the same curvature, there is overlap between the ultrasonic beam deflected in the minor axis direction and the ultrasonic beam not deflected. , If the inserted needle tip is included in both ultrasonic beams, it may not be possible to determine which ultrasonic beam the position of the puncture needle is in, and the position of the puncture needle is more accurate. There is a request for easy recognition.

An object of the present invention is to accurately and easily recognize the position of a recognition object such as a puncture needle in a subject.

In order to solve the above problems, the ultrasonic probe according to claim 1 is
Multiple oscillators that are arranged in multiple long-axis rows arranged in the short-axis direction and transmit and receive ultrasonic waves,
The acoustic lens through which the ultrasonic waves pass and
A switching element for switching on / off of input of a drive signal and output of a received signal to the vibrator in each row is provided.
The acoustic lens has a shape in which a plurality of ultrasonic beams transmitted and received by the vibrators in the respective rows are exclusively formed without overlapping each other up to a first predetermined depth.

The invention according to claim 2 is the ultrasonic probe according to claim 1.
The acoustic lens has a shape that exclusively forms a plurality of ultrasonic beams transmitted and received by the vibrators in each row up to the first predetermined depth with almost no gap.

The invention according to claim 3 is the ultrasonic probe according to claim 1 or 2.
The acoustic lens includes a lens unit corresponding to the vibrator in each row.
The lens portion corresponding to the vibrator in the row other than the center in the short axis direction forms an ultrasonic beam deflected to the ultrasonic beam side formed by the lens portion corresponding to the vibrator in the row in the center in the short axis direction. Has an aspherical shape.

The invention according to claim 4 is the ultrasonic probe according to claim 3.
The lens unit corresponding to the vibrator in the row other than the center in the minor axis direction has a second predetermined depth deeper than the first predetermined depth toward the center in the minor axis direction, in the minor axis direction. It has a curvature at which the ultrasonic beam of the lens portion corresponding to the center and the oscillators in the non-center row is focused.

The ultrasonic diagnostic apparatus according to claim 5 is the ultrasonic diagnostic apparatus according to claim 5.
The ultrasonic probe according to any one of claims 1 to 4,
A transmission unit that outputs a drive signal to the vibrators in each row of the ultrasonic probe through switching of the switching element.
A receiving unit that acquires a receiving signal corresponding to the vibrators in each row from the ultrasonic probe through switching of the switching element.
An image generation unit that generates ultrasonic image data corresponding to each column from a received signal corresponding to each column, and an image generation unit.
It includes an image processing unit that synthesizes the generated plurality of ultrasonic image data to generate composite image data.

The invention according to claim 6 is the ultrasonic diagnostic apparatus according to claim 5.
A display control unit for displaying the composite image data on the display unit is provided.

The invention according to claim 7 is the ultrasonic diagnostic apparatus according to claim 5 or 6.
The image processing unit extracts a partial image of a recognition target object from the plurality of ultrasonic image data, expresses the extracted partial image separately in each column, and expresses the plurality of ultrasonic image data. One of them and a plurality of partial images that are separately identifiable in each column are combined to generate composite image data.

The invention according to claim 8 is the ultrasonic diagnostic apparatus according to claim 7.
The expression is at least one of display color, saturation, brightness, and blinking.

According to the present invention, the position of the recognition object in the subject can be accurately and easily recognized.

It is an overall view of the ultrasonic diagnostic apparatus of embodiment of this invention. It is a block diagram which shows the internal structure of an ultrasonic diagnostic apparatus. It is a figure which shows an example of the arrangement of a vibrator in an ultrasonic probe. (A) is a schematic diagram showing a parallel method in ultrasonic guided puncture. (B) is a schematic diagram showing a crossing method in ultrasonic guided puncture. It is a figure which shows the schematic structure in the minor axis direction of an ultrasonic probe. (A) is a figure which shows the directivity with respect to the azimuth angle of the 1st, 2nd, and 3rd oscillators. (B) is a figure which shows the directivity with respect to the azimuth angle of the 1st, 2nd, and 3rd oscillators which combined the peak. It is a figure which shows the 1st, 2nd, 3rd oscillator covered with a normal acoustic lens. It is a flowchart which shows the puncture needle image display processing. (A) is a schematic top view of the ultrasonic probe showing the deviation angle of the puncture needle insertion in the parallel method. FIG. (B) is a diagram showing a composite image generated by using only the second vibrator in the parallel method. (C) is a diagram showing a composite image generated by using the first, second, and third vibrators in the parallel method. (A) is a figure which shows the composite image generated by using only the 2nd oscillator in the crossing method. (B) is a diagram showing a composite image generated by using the first, second, and third vibrators in the crossing method. It is the schematic which shows the ultrasonic beam shape by the 1st, 2nd, 3rd vibrators in the minor axis direction of an ultrasonic probe.

Embodiments of the present invention will be described in detail with reference to the accompanying drawings. The present invention is not limited to the illustrated examples.

First, with reference to FIGS. 1 and 2, the overall device configuration of the ultrasonic diagnostic device U of the present embodiment will be described. FIG. 1 is an overall view of the ultrasonic diagnostic apparatus U of the present embodiment. FIG. 2 is a block diagram showing an internal configuration of the ultrasonic diagnostic apparatus U.

As shown in FIG. 1, the ultrasonic diagnostic apparatus U includes an ultrasonic diagnostic apparatus main body 1, an ultrasonic probe 2 connected to the ultrasonic diagnostic apparatus main body 1 via a cable 5, and an object to be recognized. It is provided with a puncture needle 3 which is a treatment tool.

Here, the puncture needle 3 has a hollow long needle shape, and is inserted into the subject at an angle freely determined by an operator such as a doctor. The puncture needle 3 can be replaced with one having an appropriate thickness, length and tip shape according to the type and amount of the site (target) to be collected of the subject such as a patient or the drug to be injected. It has become. In the ultrasonic diagnostic apparatus U, an attachment portion for guiding the puncture needle 3 in the puncture direction and a guide portion fixedly provided on the ultrasonic probe 2 for guiding the puncture needle 3 in the puncture direction are provided. It may be provided.

The ultrasonic diagnostic apparatus main body 1 is provided with an operation input unit 18 and an output display unit 19. Further, as shown in FIG. 2, in addition to these, the ultrasonic diagnostic apparatus main body 1 includes a control unit 11, a transmission drive unit 12, a reception processing unit 13, a transmission / reception switching unit 14, an image generation unit 15, and an image processing unit 16. And so on. The control unit 11 outputs a drive signal to the ultrasonic probe 2 to output ultrasonic waves based on an external input operation to an input device such as a keyboard or a mouse of the operation input unit 18, and also causes an ultrasonic probe. The reception signal related to the ultrasonic reception is acquired from the child 2, various processes are performed, and the result or the like is displayed on the display screen of the output display unit 19 or the like as necessary.

The control unit 11 includes a CPU (Central Processing Unit), an HDD (Hard Disk Drive), a RAM (Random Access Memory), and the like. The CPU reads various programs stored in the HDD, loads them into the RAM, and controls the operation of each part of the ultrasonic diagnostic apparatus U according to the programs. The HDD stores a control program for operating the ultrasonic diagnostic apparatus U, various processing programs, various setting data, and the like. In particular, the HDD stores a puncture needle image display program for performing the puncture needle image display process described later. In addition to the HDD, these programs and setting data may be stored in an auxiliary storage device using a non-volatile memory such as a flash memory including an SSD (Solid State Drive) so that the data can be read and written and updated. The RAM is a volatile memory such as an SRAM or a DRAM, which provides a memory space for work to the CPU and stores temporary data.

The transmission drive unit 12 outputs a drive signal supplied to the ultrasonic probe 2 according to a control signal input from the control unit 11, and causes the ultrasonic probe 2 to transmit ultrasonic waves. The transmission drive unit 12 includes, for example, a clock generation circuit, a pulse width setting unit, a pulse generation circuit, and a delay circuit. The clock generation circuit is a circuit that generates a clock signal that determines the transmission timing and transmission frequency of the pulse signal. The pulse width setting unit sets the waveform (shape), voltage amplitude, and pulse width of the transmission pulse output from the pulse generation circuit. The pulse generation circuit generates a transmission pulse as a drive signal based on the setting of the pulse width setting unit, and outputs it to a different wiring path for each individual vibrator 210 of the ultrasonic probe 2. The delay circuit counts the clock signals output from the clock generation circuit, and when the set delay time elapses, the delay circuit generates a transmission pulse in the pulse width generation circuit and outputs the transmission pulse to each wiring path.

The reception processing unit 13 is a circuit that acquires the reception signal input from the ultrasonic probe 2 under the control of the control unit 11. The reception processing unit 13 includes, for example, an amplifier, an A / D (Analog to Digital) conversion circuit, and a phasing addition circuit. The amplifier is a circuit that amplifies the received signal corresponding to the ultrasonic wave received by each vibrator 210 of the ultrasonic probe 2 at a predetermined amplification factor set in advance. The A / D conversion circuit is a circuit that converts an amplified reception signal into digital data at a predetermined sampling frequency. The phase-adjusting addition circuit adjusts the time phase by giving a delay time for each wiring path corresponding to each oscillator 210 to the A / D-converted received signal, and adds (phase-adjusting addition) these to sound. It is a circuit that generates line data.

Based on the control of the control unit 11, the transmission / reception switching unit 14 causes the transmission drive unit 12 to transmit a drive signal to the vibrator 210 when the ultrasonic wave is emitted (transmitted) from the vibrator 210, while the vibrator 210 emits the ultrasonic wave. When acquiring the signal related to the ultrasonic wave, the switching operation for outputting the received signal to the reception processing unit 13 is performed.

The image generation unit 15 generates a diagnostic image based on the received ultrasonic wave data. The image generation unit 15 detects the sound line data input from the reception processing unit 13 (envelope detection) to acquire a signal, and also performs logarithmic amplification and filtering (for example, low frequency transmission, smoothing, etc.) as necessary. ) And emphasis processing. As one of the diagnostic images, the image generation unit 15 scans the signal transmission direction (subject depth direction) and the ultrasonic waves transmitted by the ultrasonic probe 2 with a brightness signal corresponding to the signal strength. Each frame image data related to the B (Brightness) mode display as a tomographic image representing the two-dimensional structure in the cross section including the direction (lateral direction, long axis direction of the two-dimensional arrangement of the vibrator 210) is generated. At this time, the image generation unit 15 can adjust the dynamic range related to the display, perform gamma correction, and the like. The image generation unit 15 can be configured to include a dedicated CPU and RAM used for these image generation. Alternatively, the image generation unit 15 is provided with a dedicated hardware configuration related to image generation formed on a substrate (ASIC (Application-Specific Integrated Circuit) or the like) or formed by an FPGA (Field Programmable Gate Array). You may be. Alternatively, the image generation unit 15 may have a configuration in which processing related to image generation is performed by the CPU and RAM of the control unit 11.

The image processing unit 16 includes a storage unit 161 and a puncture needle identification unit 162. The storage unit 161 stores diagnostic image data (frame image data) processed by the image generation unit 15 and used for real-time display and display similar thereto for the most recent predetermined number of frames. The storage unit 161 is, for example, a volatile memory such as a DRAM (Dynamic Random Access Memory). Alternatively, the storage unit 161 may be various non-volatile memories capable of high-speed rewriting. The diagnostic image data stored in the storage unit 161 is read out under the control of the control unit 11 and transmitted to the output display unit 19 or output to the outside of the ultrasonic diagnostic apparatus U via a communication unit (not shown). Or something. At this time, when the display method of the output display unit 19 is the television method, a DSC (Digital Scan Converter) is provided between the storage unit 161 and the output display unit 19, and the scan format is converted before output. It should be done.

The puncture needle identification unit 162 generates image data for identifying the position of the puncture needle 3, performs appropriate processing on the image data, and extracts a needle portion image of the position including the tip portion of the puncture needle 3. The identified and extracted needle partial image of the puncture needle 3 is colored. The puncture needle identification unit 162 may use the CPU and RAM of the image processing unit 16 in common, or may be provided with a dedicated CPU and RAM, respectively. Alternatively, the puncture needle identification unit 162 may perform various processes by the CPU and RAM of the control unit 11. The puncture needle identification unit 162 can store the identified tip position information of the puncture needle 3 as a history.

As a method for identifying the position of the puncture needle 3, for example, as described in Japanese Patent No. 6123458, motion evaluation information indicating motion evaluation by taking differences and correlations between frames from ultrasonic image data of a plurality of frames. Is generated, the movement speed of the tip of the puncture needle is calculated, the position of the tip of the puncture needle is detected from the movement speed of the tip of the puncture needle and the movement evaluation information, and the position of the puncture needle including the tip is identified. be. Alternatively, the position of the subsequent tip may be estimated based on the movement history of the tip of the puncture needle 3, the tip may be detected based on the estimated position, and the position of the puncture needle including the tip may be identified. Further, the operator selects a contour similar to the selected contour by input operation to the operation input unit 18 from the candidates first obtained by contour detection, and the puncture needle is based on the above-mentioned estimated position. It may be possible to detect the position of.

The operation input unit 18 includes a push button switch, a keyboard, a mouse or a trackball, or a combination thereof, converts a user's input operation into an operation signal, and inputs the user's input operation to the ultrasonic diagnostic apparatus main body 1.

The output display unit 19 uses any of various display methods such as an LCD (Liquid Crystal Display), an organic EL (Electro-Luminescent) display, an inorganic EL display, a plasma display, and a CRT (Cathode Ray Tube) display. It includes a screen and its drive unit. The output display unit 19 generates a drive signal for the display screen (each display pixel) according to the control signal output from the CPU 15 and the image data generated by the image processing unit 16, and displays a menu related to ultrasonic diagnosis on the display screen. , Status and measurement data based on the received ultrasonic waves are displayed. Further, the output display unit 19 may be provided with an LED (Light Emitting Diode) lamp or the like separately to display whether or not the power is turned on.

The operation input unit 18 and the output display unit 19 may be integrally provided in the housing of the ultrasonic diagnostic apparatus main body 1, an RGB cable, a USB (Universal Serial Bus) cable, or HDMI. It may be attached to the outside via a (High-Definition Multimedia Interface) cable (registered trademark: HDMI) or the like. Further, if the ultrasonic diagnostic apparatus main body 1 is provided with an operation input terminal and a display output terminal, conventional peripheral devices for operation and display may be connected to these terminals for use.

The ultrasonic probe 2 emits ultrasonic waves (here, about 1 to 30 MHz) and emits them to a subject such as a living body, and the reflected waves (reflected waves reflected by the subject among the emitted ultrasonic waves). It functions as an acoustic sensor that receives (echo) and converts it into an electrical signal.

The ultrasonic probe 2 includes a plurality of vibrators 210 for transmitting and receiving ultrasonic waves, a plurality of switching elements 230 corresponding to the vibrators 210, and a switching setting unit 24. Here, it is assumed that the ultrasonic probe 2 emits ultrasonic waves from the outside (body surface) to the inside of the subject and receives the reflected waves. However, the ultrasonic probe 2 is a gastrointestinal tract. It also includes those of a size and shape that are used by inserting them into the inside of a blood vessel or the body cavity. The operator operates the ultrasonic diagnostic apparatus U by bringing the ultrasonic wave transmitting / receiving surface of the ultrasonic probe 2, that is, the surface in the direction of emitting ultrasonic waves from the transducer 210 into contact with the subject at a predetermined pressure. And perform ultrasonic diagnosis.

The number of oscillators of the oscillator 210 can be set arbitrarily. Further, in the present embodiment, the electronic scanning probe of the linear scanning method is adopted for the ultrasonic probe 2, but either the electronic scanning method or the mechanical scanning method may be adopted, and the linear scanning method, Either a sector scanning method or a convex scanning method can be adopted.

The vibrator 210 is a plurality of vibrators including a piezoelectric element having a piezoelectric body and electrodes provided at both ends where electric charges appear due to deformation (expansion and contraction) of the piezoelectric body.

By supplying a voltage pulse as a drive signal to each of the plurality of vibrators 210, the piezoelectric body of the vibrator to which the voltage pulse is supplied is deformed (expanded and contracted) according to the electric field generated in the piezoelectric body. Then, ultrasonic waves are transmitted. The transmitted ultrasonic waves depend on the position and direction of the vibrators 210 included in the predetermined number of vibrator trains to which the voltage pulses are supplied, the focusing direction of the transmitted ultrasonic waves, and the magnitude of the timing deviation (delay). It is emitted in the correct position and direction. Further, when an ultrasonic wave (reflected wave in a subject) in a predetermined frequency band is incident on the vibrator 210, the thickness of the piezoelectric body fluctuates (vibrates) due to the sound pressure, and an electric charge corresponding to the fluctuating amount is generated. It is generated, converted into an electric signal according to the amount of electric charge, and output as a received signal.

The switching setting unit 24 stores the setting of the transmission / reception sequence of the vibrator 210 for transmitting / receiving ultrasonic waves over the short axis direction (elevation direction) of the two-dimensional array of the vibrator 210, and each vibration according to the setting. The switching element 230 corresponding to the child 210 is switched on and off. The transmission / reception sequence of the vibrator 210 will be described later.

The cable 5 has a connector (not shown) with the ultrasonic diagnostic apparatus main body 1 and a connector (not shown) with the ultrasonic probe 2 at both ends thereof, and the ultrasonic probe 2 is the cable 5. It is configured to be removable from the ultrasonic diagnostic apparatus main body 1. The cable 5 may be formed integrally with the ultrasonic probe 2.

Here, a more detailed configuration and operation of the ultrasonic probe 2 will be described with reference to FIGS. 3 to 7. FIG. 3 is a diagram showing an example of the arrangement of the vibrators 210 in the ultrasonic probe 2. FIG. 4A is a schematic view showing a parallel method in ultrasonic guided puncture. FIG. 4B is a schematic view showing a crossing method in ultrasonic guided puncture. FIG. 5 is a diagram showing a schematic configuration of the ultrasonic probe 2 in the minor axis direction. FIG. 6A is a diagram showing the directivity of the vibrators VA, VB, and VC with respect to the azimuth angle. FIG. 6B is a diagram showing the directivity of the vibrators VA, VB, and VC with the peaks combined with respect to the azimuth angle. FIG. 7 is a diagram showing oscillators VA, VB, and VC covered with a normal acoustic lens 220D.

As shown in FIG. 3, in the ultrasonic diagnostic apparatus U, the vibrator 210 has a two-dimensional plane (not a plane) defined by a predetermined lateral direction (scanning direction) and an elevation direction orthogonal to the lateral direction. There are a plurality of oscillators arranged in a matrix within (may be). Normally, the number of arrangements of the vibrators 210 in the lateral direction is larger than the number of arrangements of the vibrators 210 in the elevation direction, the lateral direction is the major axis direction, and the elevation direction is the minor axis direction. The vibrator 210 has a group of vibrators in three rows (rows a, b, c) in the minor axis direction, and a plurality of stages (stages 1, 2, ...) Of vibrators are arranged in each row in the major axis direction. There is. Here, the oscillator group in the column a is conveniently referred to as the oscillator VA, and similarly, the oscillator group in the columns b and c is referred to as the oscillators VB and VC for the sake of convenience. Further, one oscillator in the stage x and the column y is expressed as an oscillator Vxy.

When generating a normal B mode (fault) image, ultrasonic waves are transmitted and received while sequentially shifting the vibrators driven in the major axis direction using the vibrator VB in row b.

Here, the parallel method and the crossing method will be described as the puncture method of the puncture needle 3 under ultrasonic guidance with reference to FIGS. 4 (a) and 4 (b).

As shown in FIG. 4A, the parallel method is a method in which the puncture needle 3 is inserted parallel to the target T in the longitudinal direction, such as tissue acquisition by puncturing the subject SU. As shown in FIG. 4B, the crossing method is a method of inserting the puncture needle 3 in a direction orthogonal to the long axis direction toward the target T of the subject SU. The parallel method and the crossing method are used properly depending on the application. Which method is used is often determined by the site to be punctured and the purpose of puncture, but it may be selected based on the experience value of the operator.

In the parallel method, when the puncture needle is inserted, the puncture needle is punctured into the subject SU from the long axis end of the ultrasonic probe, and the puncture needle is formed by a row of long axis puncture needles corresponding to the vibrator VB. It means that the needle is puncturing deep in the fault plane. At this time, if the puncture needle 3 deviates from the tomographic plane in the minor axis direction, the puncture needle 3 cannot be depicted by the conventional ultrasonic diagnostic apparatus.

In the crossing method, the puncture needle 3 is obliquely inserted into the subject SU from the short axis side of the ultrasonic probe, and is inserted into the target T directly under the ultrasonic probe. In the conventional crossing method, when a general ultrasonic probe is used, the puncture needle 3 pierced on the body surface is not displayed in the ultrasonic image even at a considerable depth, and in the immediate vicinity of the target T, For the first time, an image of a puncture needle appears on an ultrasound image. Therefore, it is difficult to know whether the puncture needle 3 that has been inserted is moving in the correct direction.

In the present embodiment, in order to capture the puncture needle 3 in a wide area in both the parallel method and the crossing method, in addition to the frame of the ultrasonic image by the vibrator VB at the same time, the ultrasonic wave by the vibrator VA It is assumed that the frame of the image and the frame of the ultrasonic image by the vibrator VC are obtained.

As shown in FIG. 5, the ultrasonic probe 2 corresponds to the acoustic lens 220, the vibrators VA, VB, and VC, and the vibrators VA, VB, and VC, respectively, in the short axis direction when viewed from the long axis end. It has switches SWA, SWB, and SWC of the switching element 230. The acoustic matching layer arranged between the acoustic lens 220 and the vibrators VA, VB, and VC, and the backing material arranged on the side opposite to the ultrasonic emission direction of the vibrators VA, VB, and VC are shown in the figure. Is omitted.

The acoustic lens 220 is an aspherical lens that focuses ultrasonic beams (transmitted ultrasonic waves) emitted from the vibrators VA, VB, and VC. The acoustic lens 220 is emitted from the lens unit 221A through which the ultrasonic beam Ba emitted from the vibrator VA passes, the lens unit 221B through which the ultrasonic beam Bb emitted from the vibrator VB passes, and the vibrator VC. It has a lens portion 221C through which the ultrasonic beam Bc passes.

The switch SWA is a switch capable of independently turning on / off the input of the drive signal and the output of the received signal from the transmission / reception switching unit 14 to each vibrator of the vibrator VA via the switching setting unit 24 and the cable 5. The switch SWB is a switch capable of independently turning on / off the input of the drive signal and the output of the received signal from the transmission / reception switching unit 14 to each vibrator of the vibrator VB via the switching setting unit 24 and the cable 5. The switch SWC is a switch capable of independently turning on / off the input of the drive signal and the output of the received signal from the transmission / reception switching unit 14 to each oscillator of the oscillator VC via the switching setting unit 24 and the cable 5.

Further, in the present embodiment, the vibrators VA, VB, and VC are arranged so that the ultrasonic beams Ba, Bb, and Bc do not substantially overlap to a certain depth and there are no gaps.

The minor axis width of the vibrator VB is wide enough to withstand normal ultrasonic scanning. It is assumed that the lens portion 221B of the acoustic lens 220 that covers the vibrator VB has a beam forming ability that can be used for normal ultrasonic scanning. The minor axis width of the vibrators VA and VC may be narrower than that of the vibrator VB, but the width is sufficient to obtain the reflected wave (echo) of the punctured needle 3 inserted. The lens portions 221A and 221C of the acoustic lens 220 that covers the vibrators VA and VC preferably have an aspherical shape having a larger radius of curvature than the lens portion 221B, but an obliquely flat shape can also be used. be. Further, although it is not impossible to have a flat shape instead of an oblique shape, it is desirable that the shape is oblique in consideration of the fusion with the ultrasonic beam Bb by the vibrator VB described later. Even if the lens shape of the lens portion 221B is an aspherical shape, it can be smoothly connected to the lens portions 221A and 221C as long as there is no inconvenience in normal ultrasonic scanning (for example, the side lobe becomes large). good.

In order to accurately capture the position of the puncture needle 3, it is desirable that the positions occupied by the ultrasonic beams Ba, Bb, and Bc transmitted and received by the vibrators VA, VB, and VC are exclusive. By being exclusive, the reflected wave (echo) from the puncture needle 3 is included only in the reflected wave from any one of the vibrators VA, VB, and VC, so that it is easy to discriminate.

However, since the directivity of the ultrasonic beam has a shape having a gentle base, the ultrasonic beams Ba, Bb, and Bc overlap at the base, and therefore, as shown in FIG. 5, they are completely exclusive. It does not become. FIG. 6A shows the overlap of the ultrasonic beams Ba, Bb, and Bc at a certain depth. In FIG. 6A, the horizontal axis shows the azimuth in the short axis direction, the vertical axis shows the directivity, and the beam shapes of the ultrasonic beams Ba, Bb, and Bc by the vibrators VA, VB, and VC are shown. There is. In order to facilitate the determination of which ultrasonic beam contains the reflected wave of the piercing needle 3, it is preferable that the adjacent ultrasonic beams have the same level (points ab and bc in FIG. 6A). ) Is -6 [dB] to -12 [dB] from the peak of the transmitted or received ultrasonic beam.

Regarding the peak of the ultrasonic beam, it is desirable to use the peak of the ultrasonic beam Bb by the vibrator VB as a reference. For example, the short axis width of the vibrators VA and VC is larger than the short shaft width of the vibrator VB. When it is narrow, it is assumed that the heights of the ultrasonic beams Ba and Bc are lower than the peak heights of the ultrasonic beams Bb. The difference in height of the ultrasonic beam can be obtained by calculation in advance and can be corrected by using the calculated value. FIG. 6B shows that the heights of the directivity peaks of the vibrators VA and VC of FIG. 6A are aligned with the heights of the directivity of the vibrator VB. When there is a large difference in sensitivity between the vibrators, the needle position can be accurately captured in this way. Further, since the difference in sensitivity between the vibrators also occurs depending on the depth, if the difference is large, correction may be performed.

Here, an appropriate shape of the acoustic lens 220 according to the present embodiment will be described. First, as shown in FIG. 7, consider a configuration in which the vibrators VA, VB, and VC are covered with an acoustic lens 220D in which a normal short-axis lens is simply connected. In this case, the ultrasonic beams from the respective transducers VA, VB, and VC have parallel directivity as shown by the arrows. However, in the ultrasonic beam of the vibrator VB, the ultrasonic beam becomes thinner from the vicinity of the vibrator VB toward the focal point. That is, the ultrasonic beam produced by the vibrators VA and VC needs to fill the left and right sides of the thinned ultrasonic beam of the vibrator VB (have directivity). There is a gap (strictly speaking, both) in the directivity of the ultrasonic beam of the vibrator VA and the ultrasonic beam of the vibrator VB, or in the directionality of the ultrasonic beam of the vibrator VC and the ultrasonic beam of the vibrator VB. If there is a zone in which the sensitivity of the ultrasonic beam is low), it becomes difficult to capture the puncture needle 3 when it is located in that portion. Therefore, it is desirable that the lens shape of the acoustic lens is such that the ultrasonic beam by the vibrator VA and the ultrasonic beam by the vibrator VC are deflected inward.

However, when the ultrasonic beams of the vibrators VA and VC are focused at a shallow position close to the vibrators VA and VC, the punctured needle 3 that has been inserted does not easily enter the ultrasonic beam in the crossing method puncture. That is, it cannot be captured. Considering this, it is desirable that the ultrasonic beams of the vibrators VA and VC are deflected, but the focusing position is deep or not focused.

When an acoustic lens having a lens shape such that the ultrasonic beam by the vibrator VA and the ultrasonic beam by the vibrator VC is deflected inward is used, the ultrasonic beam by the vibrators VA and VC becomes deeper. Overlaps with the central ultrasonic beam by the vibrator VB, making it impossible to determine the position of the piercing needle 3. Therefore, it is desirable that the ultrasonic beams by the vibrators VA, VB, and VC are separated so that the deflection angle is not too large and the needle position can be determined to a depth where there is no clinical problem.

The depth of separation depends on the diagnostic site, but when a high-frequency linear probe is used as the ultrasonic probe 2, it is desirable that the separation can be performed up to 25 to 30 [mm]. Examples of the shape of the acoustic lens that meets the above conditions include the lens shape of the aspherical acoustic lens 220 as shown in FIG. In the acoustic lens 220, the lens portion 221B corresponding to the transducer VB has a tight curvature (the radius of curvature is small), and the lens portions 221A and 221C corresponding to the transducers VA and VC have a loose curvature (the radius of curvature is large). It has a shape.

In the parallel method, as shown in FIG. 5, an acoustic lens 220 is used, but when the switch SWB is turned on and the switches SWA and SWC are turned off, ultrasonic waves are transmitted and received using the vibrator VB. In this case, the operation is the same as that of the conventional ultrasonic diagnostic apparatus for transmitting and receiving ultrasonic waves, as described above.

If the switch SWA is turned on and the switches SWB and SWC are turned off, ultrasonic waves are transmitted and received by the vibrator VA, but the lens portion 221A corresponding to the vibrator VA has a substantially oblique aspherical shape. Therefore, the transmission / reception beam of ultrasonic waves is deflected toward the center of the vibrator, and the intersection of the transmission / reception beam and the center line is located far from the focusing point of the lens unit 221B corresponding to the vibrator VB. When the lens portions 221A and 221C are provided with a curvature, it is desirable that the curvature be such that the lens portions 221A and 221C are focused near this intersection. The transmission / reception beams of the ultrasonic waves formed by the acoustic lens 220 and the vibrators VA, VB, and VC do not overlap each other up to a desired depth, and there is no gap (blind spot on sensing). In the present embodiment, in the parallel method, in order to form a tomographic image using the vibrator VB and a tomographic image using each of the vibrators VA and VC, the puncture needle deviated from the tomographic image plane by the vibrator VB. It is possible to capture.

Regarding the crossing method, as shown in FIG. 4B, in the ultrasonic probe 2 of the present embodiment, the target T in the subject SU is in the tomographic image by the vibrator VB. On the other hand, the puncture needle 3 that has been inserted can be captured in the tomographic image by the vibrator VA (or the vibrator VC) much earlier than when a normal ultrasonic probe is used. As an example, when puncturing a target with a puncture angle of 45 degrees and a depth of 1 cm, assuming that the ultrasonic beam width of the vibrator VB is 1.8 mm, with a normal ultrasonic probe, at about 1 mm in front of the target. While the puncture needle was shown for the first time, the ultrasonic probe 2 of the present embodiment could be confirmed from about 4 mm in front. As described above, when the crossing method of the present embodiment is performed, the position of the puncture needle 3 can be confirmed considerably before the target T, and the puncture operation can be facilitated.

Here, the transmission / reception sequence of the vibrator 210 of the present embodiment will be described with reference to FIG. As described above, in the configuration using the acoustic lens 220, the vibrators VA, VB, VC, and the switches SWA, SWB, SWC, the reflected wave (echo) of the piercing needle 3 deviating from the ultrasonic beam Bb formed by the vibrator VB. ) Is transmitted and received using the vibrators VA and VB, and the scanning (ultrasonic wave transmission and reception) in this case is, for example, the vibrators V1a, V1b, V1c, V2a, V2b, V2c, V3a. , V3b, V3c ... Such a scanning sequence is stored in the switching setting unit 24.

However, in this case, since the number of transmissions and receptions is tripled, the frame rate of the B-mode tomographic image display is reduced to one-third. Therefore, the scanning of the vibrators VA and VC for capturing the puncture needle 3 is thinned out, and for example, the vibrators V1a, V1b, V1c, V2b, V3a, V3b, V3c, V4b, V5a, V5b, V5c ... It is also possible to suppress the decrease in frame rate. In the above description, a case where one oscillator is used for scanning in the major axis direction is described for simplification, but in reality, a plurality of oscillators are used for forming a transmission / reception beam in the major axis direction. In addition to this, it is also possible to apply a method such as increasing the frame rate by using parallel reception in the long axis direction, which is already known.

Next, the operation of the ultrasonic diagnostic apparatus U will be described with reference to FIGS. 8 to 11. FIG. 8 is a flowchart showing the puncture needle image display process. FIG. 9A is a schematic top view of the ultrasonic probe 2 showing the deviation angle θ of the puncture needle 3 in the parallel method. FIG. 9B is a diagram showing an ultrasonic image generated by using only the vibrator VB in the parallel method. FIG. 9C is a diagram showing a composite image generated by using the vibrators VA, VB, and VC in the parallel method. FIG. 10A is a diagram showing an ultrasonic image generated by using only the vibrator VB in the crossing method. FIG. 10B is a diagram showing a composite image generated by using the vibrators VA, VB, and VC in the crossing method. FIG. 11 is a schematic view showing an ultrasonic beam Bbc by vibrators VA, VB, and VC in the short axis direction of the ultrasonic probe 2.

The puncture needle image display process executed by the ultrasonic diagnostic apparatus U will be described with reference to FIG. In the puncture needle image display processing, when an operator such as a doctor performs a puncture operation of inserting the puncture needle 3 into the target T as a target for acquiring the tissue of the subject SU, the puncture needle 3 in the subject This is a process of assisting the puncture work by displaying the B-mode tomographic image live.

In advance, for example, an operator such as a doctor waits in an examination room provided with an ultrasonic diagnostic apparatus U, a patient as a subject SU enters the examination room, lays down on a bed, and uses a puncture needle 3. It shall be ready for the puncture work that was done. Then, the ultrasonic diagnostic apparatus U receives various setting information input such as a frame rate in the puncture needle image display process and an execution instruction of the puncture needle image display process from the operator via the operation input unit 18 as a trigger. , The control unit 11 executes the puncture needle image display process according to the puncture needle image display program stored in the ROM.

First, the control unit 11 causes the transmission drive unit 12 to start generating a drive signal, and the drive signal is switched by switching the switching element 230 according to the transmission / reception sequence stored in the switching setting unit 24 via the transmission / reception switching unit 14. Is input to each of the vibrators VA, VB, and VC to emit transmitted ultrasonic waves, receive reflected ultrasonic waves (echo), and acquire a received signal to the reception processing unit 13 via the transmission / reception switching unit 14. (Step S11). As for the received signal obtained in step S11, the received signals for each frame at the same time corresponding to the vibrators VA, VB, and VC are acquired in the order corresponding to the transmission / reception sequence.

Then, the control unit 11 causes the image generation unit 15 to generate one frame of B-mode image data from the reception signal corresponding to the vibrator VA input from the reception processing unit 13 in step S11 (step S12). Then, the control unit 11 extracts the needle portion image of the puncture needle 3 from the B mode image data corresponding to the vibrator VA generated in step S12 by the puncture needle identification unit 162 (discards the portion other than the needle portion image). ) (Step S13). Then, the control unit 11 colors the needle portion image of the image data generated in step S13 with red color indicating the vibrator VA by the puncture needle identification unit 162 (step S14).

Further, the control unit 11 causes the image generation unit 15 to generate one frame of B-mode image data from the reception signal corresponding to the vibrator VC input from the reception processing unit 13 in step S11 (step S15). The B-mode image data generated in step S15 is a frame at the same time as the B-mode image data generated in step S12. Then, the control unit 11 extracts the needle partial image of the puncture needle 3 from the B mode image data corresponding to the vibrator VC generated in step S15 by the puncture needle identification unit 162 (step S16). Then, the control unit 11 colors the needle portion image of the image data generated in step S16 with green indicating the vibrator VC by the puncture needle identification unit 162 (step S17).

Further, the control unit 11 causes the image generation unit 15 to generate one frame of B-mode image data from the reception signal corresponding to the vibrator VB input from the reception processing unit 13 in step S11 (step S18). The B-mode image data generated in step S18 is a frame at the same time as the B-mode image data generated in steps S12 and S15. Then, the control unit 11 extracts the needle partial image of the puncture needle 3 from the B mode image data corresponding to the vibrator VB generated in step S18 by the puncture needle identification unit 162 (step S19). Then, the control unit 11 colors the needle portion image of the image data generated in step S19 with blue indicating the vibrator VB by the puncture needle identification unit 162 (step S20).

In steps S14, S17, and S20, the color of the needle portion image obtained by any of the vibrators VA, VB, and VC is different as the type of expression. The color combination in steps S14, S17, and S20 is an example, and the color combination is not limited to this, and a gradation such as green-blue-purple may be used. Further, the type of the separately identifiable expression of each needle partial image may be changed to another type. For example, as a separately identifiable expression for each needle partial image, the saturation and brightness may be different, the presence / absence of blinking and the interval may be different, or a configuration in which a plurality of types of expressions are combined may be used. good.

In steps S11, S12, S15, and S18, the processes corresponding to the various setting information initially input are executed. Further, various setting information may be appropriately changed and input from the operator via the operation input unit 18 during the execution of the puncture needle image display process. Further, the expression (color) of the needle partial image in steps S14, S17, and S20 may be input as various setting information from the operator via the operation input unit 18.

Further, after the execution of step S18, the control unit 11 acquires the normal B-mode image data of one frame generated in step S11 by the image generation unit 15 (step S21). Then, the control unit 11 has the image processing unit 16 the red needle partial image generated in step S14, the green needle partial image generated in step S17, and the blue needle partial image generated in step S20. And the 1-frame B-mode image data acquired in step S21 are combined to generate 1-frame composite image data (step S22). Then, the control unit 11 causes the image processing unit 16 to display the composite image data of one frame generated in step S22 on the output display unit 19 (step S24).

Then, the control unit 11 determines whether or not the end instruction of the puncture needle image display process has been input from the operator via the operation input unit 18 (step S24). If it does not end (step S24; NO), the process proceeds to step S11. When finished (step S24; YES), the puncture needle image display process ends.

Next, an image example of the puncture needle image display processing in the parallel method and the crossing method will be described with reference to FIGS. 9 and 10.

An image generated and displayed by the puncture needle image display process will be described with reference to FIG. 9 when the puncture operation is performed by the parallel method. First, as shown in FIG. 9A, as a parallel method, when the ultrasonic probe 2 applied to the surface of the subject SU is viewed from above, the target below the ultrasonic probe 2 is viewed. An example of inserting the puncture needle 3 into the puncture needle 3 will be described. The axial deviation of the puncture needle 3 from the center line C in the long axis direction of the ultrasonic probe 2 is expressed as the deviation angle θ of the puncture needle 3. In the state of FIG. 9A, the operator starts inserting the puncture needle 3 from the long axis end of the ultrasonic probe 2, and at this point, the position of the puncture needle 3 is aligned, but the insertion is performed. As the needle advances, the position of the puncture needle 3 deviates from the target due to the deviation angle θ.

The puncture needle 3 is inserted from the state shown in FIG. 9 (a), and the puncture needle image display process uses only the vibrator VB and has the needle partial image N12 of the puncture needle 3 shown in FIG. 9 (b). It is assumed that the ultrasonic image is displayed. That is, the composite image displayed by executing steps S11 (transmit / receive only by the vibrator VB) and steps S18 to S23 is displayed. However, in the ultrasonic image of FIG. 9 (b), blue is represented by a "checkerboard pattern", and the same applies to FIGS. 9 (c), 10 (a), and 10 (b). In the ultrasonic image of FIG. 9B, the puncture needle 3 included in the region of the ultrasonic beam of the vibrator VB is shown in blue.

Then, in the same state and at the same time as the transmission and reception of the ultrasonic image of FIG. 9B, the composite image shown in FIG. 9C is obtained by using the vibrators VA, VB, and VC in the puncture needle image display processing. rice field. However, in FIG. 9 (c), red is represented by a “shaded pattern”, and the same applies to FIG. 10 (b). In the composite image of FIG. 9B, the needle partial image N12 of the puncture needle 3 included in the ultrasonic beam region of the vibrator VB is shown in blue, and as shown by the arrow, the ultrasonic beam of the vibrator VA is super The needle partial image N11 of the puncture needle 3 included in the region of the ultrasonic beam is shown in red.

In FIG. 9B, an arrow is shown at the same position as the arrow in FIG. 9C, but the puncture needle 3 at the position of the arrow is not visible. In this way, in the parallel method, the puncture needle 3 is moved from the center line C only by adding the needle partial image of the puncture needle 3 captured by the vibrator VA (or VC) to the B mode image using the vibrator VB. It is possible to clearly and clearly indicate whether or not the deviation has occurred and which direction the deviation has occurred.

Next, as shown in FIG. 4B, as a crossing method, the puncture needle 3 is inserted into the target below the ultrasonic probe 2 from a direction forming an angle of 45 ° with the surface of the subject SU. An example will be described. The puncture needle 3 is inserted from this state, and as in the conventional method, the puncture needle image display process uses only the vibrator VB and has the needle partial image N22 of the puncture needle 3 shown in FIG. 10 (a). It is assumed that the ultrasonic image is displayed. That is, it is an ultrasonic image displayed by executing steps S11 (transmission and reception only by the vibrator VB) and steps S18 to S23.

Then, in the same state and at the same time as the transmission and reception of the ultrasonic image of FIG. 10 (a), the composite image shown in FIG. 10 (b) is obtained by using the vibrators VA, VB, and VC in the puncture needle image display process. rice field. However, in FIG. 10B, green is represented by "hatching". In the composite image of FIG. 10B, the needle partial image N22 of the puncture needle 3 included in the region of the ultrasonic beam of the vibrator VB is shown in blue, and the short axis of the ultrasonic tomographic image of the vibrator VB is shown. The needle partial image N21 of the puncture needle 3 included in the ultrasonic beam region of the vibrator VA is shown in red on both sides of the direction, and the needle partial image of the puncture needle 3 included in the ultrasonic beam region of the transducer VC is shown in red. N23 is shown in green. Therefore, a part of the shallow puncture needle 3 shown in green on the oscillator VC side, a part of the puncture needle 3 indicated in blue near the depth of the target corresponding to the oscillator VB, and the oscillator VA side. A part of the deep puncture needle 3 shown in red is continuously visible as one object.

In this way, in the crossing method, the visible range of the puncture needle 3 can be expanded only by adding the needle partial image of the puncture needle 3 captured by the vibrators VA and VC to the ultrasonic image using the vibrator VB. The depth of the puncture needle 3 can be clearly indicated by a color, and a safe puncture operation can be performed.

The puncture needle image display process uses all of the vibrators VA, VB, and VC for ultrasonic image generation, but it is preferable to improve the deep depiction ability.

Regarding the method of drawing a relatively shallow part using the center vibrator in the short axis direction of a plurality of two-dimensionally arranged vibrators and drawing a relatively deep part using all the vibrators in the short axis direction. , Already known. As shown in FIG. 11, in the ultrasonic probe 2, the focal distance of the ultrasonic beam Bab generated by using all the vibrators VA, VB, VC in the short axis direction and the acoustic lens 220 is in the short axis direction. It is longer than the focal distance of the ultrasonic beam Bb generated by using the vibrator VB at the center of the lens and the lens portion 221B of the acoustic lens 220.

When the ultrasonic probe 2 is used to depict a relatively deep part, the ultrasonic beam Bac moves the entire short axis direction at the depth desired to depict the lens portions 221A and 221C corresponding to the vibrators VA and VC. By passing through the center of the vibrator (the position of the ultrasonic beam Bb of the vibrator VB) and by giving a curvature so that the ultrasonic beam Bbc focuses at the depth to be visualized, deep depiction is performed. It is desirable because it can improve the ability. The depth at which this drawing is desired is deeper than the predetermined depth at which the ultrasonic beams Ba, Bb, and Bc corresponding to the vibrators VA, VB, and BC are exclusive.

As described above, according to the present embodiment, the ultrasonic probes 2 are arranged in three rows a, b, and c in the major axis direction arranged in the minor axis direction, and a plurality of vibrators VA for transmitting and receiving ultrasonic waves. , VB, VC, an acoustic lens 220 through which ultrasonic waves pass, and a switching element that turns on / off the input of drive signals and the output of received signals to the vibrators VA, VB, and VC of rows a, b, and c. 230 (switches SWA, SWB, SWC) and. The acoustic lens 220 has a shape that exclusively forms a plurality of ultrasonic beams Ba, Bb, and Bc transmitted and received by the vibrators VA, VB, and VC in each row up to a first predetermined depth. The first predetermined depth is a depth according to the diagnosis site, for example, 25 to 30 [mm].

Therefore, by synthesizing the B-mode image data of each of the columns a, b, and c generated by switching the vibrators VA, VB, and VC of the columns a, b, and c, the treatment tool is used in the composite image. The position of the puncture needle 3 inserted into the subject can be accurately and easily recognized.

Further, the acoustic lens 220 has a shape that exclusively and almost without gaps form a plurality of ultrasonic beams Ba, Bb, Bc transmitted and received by the vibrators VA, VB, and VC in each row up to the first predetermined depth. .. Therefore, it is possible to reduce the region where the puncture needle 3 cannot be seen in the composite image obtained by synthesizing the B-mode image data of each of the columns a, b, and c.

Further, the acoustic lens 220 includes lens units 221A, 221B, 221C corresponding to the vibrators VA, VB, and VC of the rows a, b, and c. The lens units 221A and 221C corresponding to the vibrators VA and VC in the rows a and c other than the center in the short axis direction are ultrasonic waves formed by the lens unit 221B corresponding to the vibrator VB in the center row b in the short axis direction. It has an aspherical shape that forms ultrasonic beams Ba and Bc that deflect toward the beam Bb side. Therefore, a plurality of ultrasonic beams Ba, Bb, and Bc transmitted and received by the vibrators VA, VB, and VC of the rows a, b, and c up to the first predetermined depth can be easily formed exclusively and without gaps.

Further, the lens portions 221A and 221C corresponding to the vibrators VA and VC in the rows a and c other than the center in the minor axis direction have a curvature of focusing at the center in the minor axis direction at a second predetermined depth. The second predetermined depth is deeper than the first predetermined depth, and is a depth at which a high depiction is desired to be performed. Therefore, in the composite image data using all of the vibrators VA, VB, and VC, the depiction ability can be improved at a desired second predetermined depth.

Further, the ultrasonic diagnostic apparatus U is driven by the vibrators VA, VB, and VC of the rows a, b, and c of the ultrasonic probe 2 via the switching between the ultrasonic probe 2 and the switching element 230. Reception that acquires the reception signal corresponding to the transducers VA, VB, VC of each row a, b, c from the ultrasonic probe 2 through the transmission drive unit 12 that outputs a signal and the switching of the switching element 230. The processing unit 13, the image generation unit 15 that generates B-mode image data corresponding to each column a, b, c from the received signals corresponding to each column a, b, c, and a plurality of generated B-mode image data. Is provided with an image processing unit 16 that synthesizes the above and generates composite image data. Therefore, the position of the puncture needle 3 in the subject can be accurately and easily recognized in the composite image of the B mode image data using the vibrators VA, VB, and VC of the columns a, b, and c.

Further, the control unit 11 displays the composite image data on the output display unit 19. Therefore, the position of the puncture needle 3 in the subject can be accurately and easily recognized in the displayed composite image.

Further, the image processing unit 16 extracts the needle partial image of the piercing needle 3 from the three B mode image data corresponding to the transducers VA, VB, and VC of the rows a, b, and c, and the extracted needle partial image. Is displayed as a display color that can be identified separately in each of the columns a, b, and c, and one B-mode image data corresponding to the transducer VB of the three B-mode image data and each column a, b, A composite image data is generated by synthesizing a needle partial image having a display color that can be identified separately in c. Therefore, the position of the puncture needle 3 in the subject can be recognized more accurately and more easily due to the difference in the display color of the needle partial image. Specifically, in the parallel method, it is possible to accurately and easily visually recognize whether or not the puncture needle 3 has deviated and the deviated direction (direction of the vibrator VA side or the vibrator VC side) due to the difference in the display color of the needle partial image. can. In the crossing method, the puncture needle 3 can be largely visually recognized by the needle portion images having different display colors, and the depth of the puncture needle 3 can be accurately and easily visually recognized by the difference in the display color of the needle portion images.

The description in the above embodiment is an example of a suitable ultrasonic diagnostic apparatus according to the present invention, and is not limited thereto.

For example, in the above embodiment, the ultrasonic diagnostic apparatus U is configured to generate and display B-mode image data as ultrasonic image data, but the present invention is not limited to this. The ultrasonic diagnostic apparatus U may be configured to generate and display tomographic image data of another mode as ultrasonic image data.

Further, in the above embodiment, the ultrasonic probe 2 in which a plurality of vibrators in three rows in the long axis direction are arranged in the short axis direction has been described, but the present invention is not limited to this. Increase the number of exclusive regions by increasing the number of divisions (number of oscillators) in the minor axis direction, such as 5 rows, 7 rows, etc. in the minor axis direction, or by using multiple oscillators at the same time. Is also possible.

Further, in the above embodiment, as a recognition target, a partial image of the puncture needle 3 as a treatment tool is extracted from the ultrasonic image data and colored, but the present invention is not limited to this. For example, a configuration in which a part such as a blood vessel in a subject is set as a recognition object, a partial image of the part is extracted from ultrasonic image data and colored (in a representation that can be identified separately in each column), or a pseudo (expression) It is also possible to perform a simple) three-dimensional display.

Further, the detailed configuration and detailed operation of each part constituting the ultrasonic diagnostic apparatus U in the above embodiments can be appropriately changed without departing from the spirit of the present invention.

U Ultrasonic diagnostic device 1 Ultrasonic diagnostic device main unit 11 Control unit 12 Transmission drive unit 13 Reception processing unit 14 Transmission / reception switching unit 15 Image generation unit 16 Image processing unit 161 Storage unit 162 Puncture needle identification unit 18 Operation input unit 19 Output display unit 2 Ultrasonic probe 210, VA, VB, VC, V1a ... Transducer 220, 220D Acoustic lens 221A, 221B, 221C Lens unit 230 Switching element SWA, SWB, SWC Switch 24 Switching setting unit 3 Puncture needle 5 Cable

Claims (8)

Multiple oscillators that are arranged in multiple long-axis rows arranged in the short-axis direction and transmit and receive ultrasonic waves,
The acoustic lens through which the ultrasonic waves pass and
A switching element for switching on / off of input of a drive signal and output of a received signal to the vibrator in each row is provided.
The acoustic lens is an ultrasonic probe having a shape that exclusively forms a plurality of ultrasonic beams transmitted and received by the vibrators in each row up to a first predetermined depth without overlapping each other. The ultrasonic probe according to claim 1, wherein the acoustic lens has a shape that exclusively forms a plurality of ultrasonic beams transmitted and received by the vibrators in each row up to the first predetermined depth with almost no gap. Child. The acoustic lens includes a lens unit corresponding to the vibrator in each row.
The lens portion corresponding to the vibrator in the row other than the center in the short axis direction forms an ultrasonic beam deflected to the ultrasonic beam side formed by the lens portion corresponding to the vibrator in the row in the center in the short axis direction. The ultrasonic probe according to claim 1 or 2, which has an aspherical shape. The lens unit corresponding to the vibrator in the row other than the center in the minor axis direction has a second predetermined depth deeper than the first predetermined depth toward the center in the minor axis direction, and is in the minor axis direction. The ultrasonic probe according to claim 3, which has a curvature in which the ultrasonic beam of the lens portion corresponding to the vibrators in the center and the rows other than the center is focused. The ultrasonic probe according to any one of claims 1 to 4,
A transmission unit that outputs a drive signal to the vibrators in each row of the ultrasonic probe through switching of the switching element.
A receiving unit that acquires a receiving signal corresponding to the vibrators in each row from the ultrasonic probe through switching of the switching element.
An image generation unit that generates ultrasonic image data corresponding to each column from a received signal corresponding to each column, and an image generation unit.
An ultrasonic diagnostic apparatus including an image processing unit that synthesizes a plurality of the generated ultrasonic image data to generate a composite image data. The ultrasonic diagnostic apparatus according to claim 5, further comprising a display control unit that displays the composite image data on the display unit. The image processing unit extracts a partial image of a recognition target object from the plurality of ultrasonic image data, expresses the extracted partial image separately in each column, and expresses the plurality of ultrasonic image data. The ultrasonic diagnostic apparatus according to claim 5 or 6 , wherein one of the images and a plurality of partial images that are separately identifiable in each column are combined to generate composite image data. The ultrasonic diagnostic apparatus according to claim 7, wherein the expression is at least one of display color, saturation, brightness, and blinking.

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